Radiation detection system for neutron capture therapy system and detection method thereof

ABSTRACT

A radiation detection system and method for a neutron capture therapy system, which may increase the accuracy of neutron beam irradiation dose of the neutron capture therapy system and find out a fault position in time. The neutron capture therapy system includes a charged particle beam, a charged particle beam inlet allowing the charged particle beam to pass through, a neutron beam generating unit which may generate a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam, a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit, and a beam outlet adjacent to the beam shaping assembly, the radiation detection system includes a radiation detection device for real-time detection of γ rays instantly emitted under neutron beam irradiation.

RELATED APPLICATION INFORMATION

This application is a continuation of International Application No. PCT/CN2017/070876, filed on Jan. 11, 2017, which claims priority to Chinese Patent Application No. 201610027799.2, filed on Jan. 15, 2016; and Chinese Patent Application No. 201620042852.1, filed on Jan. 15, 2016, the disclosures of which are hereby incorporated by reference.

FIELD OF THE DISCLOSURE

The present disclosure relates generally to a radiation detection system and a radiation detection method thereof, and, more particularly, to a radiation detection system for a neutron capture therapy system and a radiation detection method thereof.

BACKGROUND OF THE DISCLOSURE

As atomics moves ahead, such radiotherapy as Cobalt-60, linear accelerators and electron beams has been one of major means to cancer therapy. However, conventional photon or electron therapy has been undergone physical restrictions of radioactive rays; for example, many normal tissues on a beam path will be damaged as tumor cells are destroyed. On the other hand, sensitivity of tumor cells to the radioactive rays differs greatly, so in most cases, conventional radiotherapy falls short of treatment effectiveness on radioresistant malignant tumors (such as glioblastoma multiforme and melanoma).

For the purpose of reducing radiation damage to the normal tissue surrounding a tumor site, target therapy in chemotherapy has been employed in the radiotherapy. While for high-radioresistant tumor cells, radiation sources with high RBE (relative biological effectiveness) including such as proton, heavy particle and neutron capture therapy have also developed. Among them, the neutron capture therapy combines the target therapy with the RBE, such as the boron neutron capture therapy (BNCT). By virtue of specific grouping of boronated pharmaceuticals in the tumor cells and precise neutron beam regulation, BNCT is provided as a better cancer therapy choice than conventional radiotherapy.

BNCT takes advantage that the boron (¹⁰B)-containing pharmaceuticals have high neutron capture cross section and produces ⁴He and ⁷Li heavy charged particles through ¹⁰B(n,α)⁷Li neutron capture and nuclear fission reaction. As illustrated in FIGS. 1 and 2, a schematic drawing of BNCT and a nuclear reaction formula of ¹⁰B (n,α) ⁷Li neutron capture are shown, the two charged particles, with average energy at about 2.33 MeV, are of linear energy transfer (LET) and short-range characteristics. LET and range of the alpha particle are 150 keV/micrometer and 8 micrometers respectively while those of the heavy charged particle ⁷Li are 175 keV/micrometer and 5 micrometers respectively, and the total range of the two particles approximately amounts to a cell size. Therefore, radiation damage to living organisms may be restricted at the cells' level. When the boronated pharmaceuticals are gathered in the tumor cells selectively, only the tumor cells will be destroyed locally with a proper neutron source on the premise of having no major normal tissue damage.

Beam detection and diagnosis which directly relates to the dose and effect of an irradiation therapy, belongs to an important subject in a neutron capture therapy system. As disclosed in the prior art, in a neutron capture therapy system, the dose of a neutron beam during irradiation is measured, for example, by attaching a gold wire for measuring a neutron beam to an irradiation object in advance, detaching the gold wire therefrom during the irradiation with a neutron beam, and measuring an amount of activated gold of the gold wire. It is intended to control (for example, stop) the neutron capture therapy system so as to irradiate the irradiation object with the neutron beam with a desired dose on the basis of the measured dose.

However, in this case, for example, when a dose rate of a neutron beam varies for some reasons after measuring the amount of activated gold of the gold wire, it may not be possible to cope with this variation and it may thus be difficult to irradiate an irradiation object with a neutron beam with a desired dose. That is to say, in the aforementioned neutron capture therapy system, the irradiation dose of the radiation cannot be detected in real time, and it cannot be decided the source of the malfunction quickly once the detection devices break down, so it's time and strength consuming of malfunction checking.

Therefore, it is necessary to provide a radiation detection system for neutron capture therapy system and detection method thereof, which capable of improving the accuracy of irradiation dose and finding the malfunction location in time.

The statements in this section merely provide background information related to the present disclosure and may not constitute prior art.

SUMMARY

The subject disclosure presents a radiation detection system for a neutron capture therapy system, and the radiation detection system may increase the accuracy of neutron beam irradiation dose of the neutron capture therapy system and find out a failure position in time. The neutron capture therapy system includes a charged particle beam, a charged particle beam inlet allowing the charged particle beam to pass through, a neutron beam generating unit which may generate a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam, a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit, and a beam outlet adjacent to the beam shaping assembly, the radiation detection system includes a radiation detection device for real-time detection of γ rays instantly emitted under neutron beam irradiation.

The γ rays instantly emitted under neutron beam irradiation are γ rays generated when a neutron capture nuclear reaction occurs between the neutron beam and other elements, and other elements may be not limited to boron-10 and elements well known in the art capable of generating γ rays when a neutron capture nuclear reaction occurs may be also included. In an embodiment of the present invention, the γ rays instantly emitted under neutron beam irradiation may be γ rays generated when a boron neutron capture reaction occurs between the neutron beam and boron-10.

The radiation detection system further includes a control device for emitting a human perception signal according to a detection result of the radiation detection device so as to confirm the next operation of the neutron capture therapy system. The human perception signal may be a signal capable of being perceived by human functional organs, such as auditory sense, visual sense, tactile sense or smell sense, and may be of one or more forms in various signals such as a sound-making alarm, an alarm light, a vibrating signal and a pungent smell emitting signal.

The neutron capture therapy system further includes an accelerator for accelerating the charged particle beam, the control device includes a control part and a display part, the control part displays the detection result of the radiation detection system through the display part and feeds the detection result back to the accelerator so as to confirm the next operation of the accelerator, and the display part may be a television, a liquid crystal display, or other common display devices.

The radiation detection device may be a fission chamber or scintillator detector for detecting γ rays, and the radiation detection system calculates the boron concentration value through a detected γ signal.

A common radiation detection system capable of realizing real-time detection has two different detection principles: fission chamber and scintillator detector. During γ ray detection, one way may be to adopt a fission chamber which is an inflatable fission chamber, and the other way may be to adopt a scintillator detector.

The boron concentration value may be calculated by means of the Formula A:

$\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$

wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value obtained after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k may be calculated by means of the Formula B:

$\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$

wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value obtained after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) may be calculated by means of the Formula C:

B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C)

wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.

For accurately judging which detection device or monitoring device breaks down, when the below detection values and the standard values have a big difference, a corresponding detection device or monitoring device may be concluded to be abnormal.

The tumor dose rate D_(T)(t) at the time t may be calculated by means of the Formula D:

D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D)

wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) may be calculated by means of the Formula E:

$\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} E} \right) \end{matrix}$

The D_(n)(t) may be calculated by means of the Formula F:

$\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$

The D_(γ)(t) may be calculated by means of the Formula G:

$\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$

wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.

The tumor dose rate D_(T)(t) at the time t also may be calculated by means of the Formula H:

$\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{nbcap},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$

wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) may be calculated by means of the Formula I, and C may be a calculated value calculated by means of the Formula J:

$\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{b}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$

wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, σ is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.

The beam shaping assembly includes a reflective body, a retarding body surrounded by the reflective body and adjacent to the neutron beam generating unit, a thermal neutron absorbing body adjacent to the retarding body, and a radiation shield arranged inside the beam shaping assembly.

The subject disclosure further presents a radiation detection method for a neutron capture therapy system, and the radiation detection method may increase the accuracy of neutron beam irradiation dose of the neutron capture therapy system and find out a failure position in time. The neutron capture therapy system includes a charged particle beam, a charged particle beam inlet allowing the charged particle beam to pass through, a neutron beam generating unit which may generate a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam, a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit, a beam outlet adjacent to the beam shaping assembly, and a radiation detection system, the neutron beam generating unit may be contained in the beam shaping assembly, the radiation detection system includes a radiation detection device, the radiation detection method includes a detection step of detecting γ rays instantly emitted under neutron beam irradiation in real time by means of the radiation detection device.

The detection method further includes a control step of controlling the next operation of the neutron capture therapy system according to a detection result obtained from the detection step.

The neutron capture therapy system further includes an accelerator for accelerating the charged particle beam, and the control step may be realized by controlling the accelerator so as to confirm the next operation of the accelerator according to the detection result obtained from the detection step.

The control device includes a display part, the detection method further includes a display step of displaying the detection result obtained from the detection step through the di splay part.

The detection method further includes a calculation step of calculating the boron concentration value according to the detection result obtained from the detection step.

The boron concentration value may be calculated by means of the Formula A:

$\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$

wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k may be calculated by means of the Formula B:

$\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$

wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) may be calculated by means of the Formula C:

B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C)

wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t0, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.

For accurately judging which detection device or monitoring device breaks down, when the below detection values and the standard values have a big difference, a corresponding detection device or monitoring device may be concluded to be abnormal.

The tumor dose rate D_(T)(t) at the time t may be calculated by means of the Formula D:

D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D)

wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and the D_(B)(t) may be calculated by means of the Formula E:

$\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} E} \right) \end{matrix}$

The D_(n)(t) may be calculated by means of the Formula F:

$\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$

The D_(γ)(t) may be calculated by means of the Formula G:

$\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$

wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.

The tumor dose rate at the time t may also be calculated by means of the Formula H:

$\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{nbcap},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$

wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) is calculated by means of the Formula I, and C may be a calculated value calculated by means of the Formula J:

$\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{b}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$

wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, σ is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t₀) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.

The subject disclosure yet presents a neutron capture therapy system, and the neutron capture therapy system includes a charged particle beam, a charged particle beam inlet allowing the charged particle beam to pass through, a neutron beam generating unit which may generate a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam, a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit, and a beam outlet adjacent to the beam shaping assembly, the neutron capture therapy system corrects the non-linear relationship between boron concentration and tumor dose.

The neutron capture therapy system includes a radiation detection system, the radiation detection system includes a radiation detection device for real-time detection of γ rays instantly emitted under neutron beam irradiation.

The γ rays instantly emitted under neutron beam irradiation are γ rays generated when a neutron capture nuclear reaction occurs between the neutron beam and other elements, and other elements may be not limited to boron-10 and elements well known in the art capable of generating γ rays when a neutron capture nuclear reaction occurs may be also included. In an embodiment of the present invention, the γ rays instantly emitted under neutron beam irradiation may be γ rays generated when a boron neutron capture reaction occurs between the neutron beam and boron-10.

The radiation detection system further includes a control device for emitting a human perception signal according to a detection result of the radiation detection device so as to confirm the next operation of the neutron capture therapy system. The human perception signal may be a signal capable of being perceived by human functional organs, such as auditory sense, visual sense, tactile sense or smell sense, and may be of one or more forms in various signals such as a sound-making alarm, an alarm light, a vibrating signal and a pungent smell emitting signal.

The neutron capture therapy system further includes an accelerator for accelerating the charged particle beam, the control device includes a control part and a display part, the control part displays the detection result of the radiation detection system through the display part and feeds the detection result back to the accelerator so as to confirm the next operation of the accelerator, and the display part may be a television, a liquid crystal display, or other common display devices.

The radiation detection device may be a fission chamber or scintillator detector for detecting γ rays, and the radiation detection system calculates the boron concentration value through a detected γ signal.

A common radiation detection system capable of realizing real-time detection has two different detection principles: fission chamber and scintillator detector. During γ ray detection, one way may be to adopt a fission chamber which is an inflatable fission chamber, and the other way may be to adopt a scintillator detector.

The boron concentration value may be calculated by means of the Formula A:

$\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$

wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value obtained after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k may be calculated by means of the Formula B:

$\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$

wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value obtained after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) may be calculated by means of the Formula C:

B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C)

wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.

For accurately judging which detection device or monitoring device breaks down, when the below detection values and the standard values have a big difference, a corresponding detection device or monitoring device may be concluded to be abnormal.

The tumor dose rate D_(T)(t) at the time t may be calculated by means of the Formula D:

D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D)

wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) may be calculated by means of the Formula E:

$\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} E} \right) \end{matrix}$

The D_(n)(t) may be calculated by means of the Formula F:

$\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$

The D_(γ)(t) may be calculated by means of the Formula G:

$\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$

wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.

The tumor dose rate D_(T)(t) at the time t also may be calculated by means of the Formula H:

$\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{nbcap},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$

wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) may be calculated by means of the Formula I, and C may be a calculated value calculated by means of the Formula J:

$\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{b}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$

wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, G is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.

The beam shaping assembly includes a reflective body, a retarding body surrounded by the reflective body and adjacent to the neutron beam generating unit, a thermal neutron absorbing body adjacent to the retarding body, and a radiation shield arranged inside the beam shaping assembly.

Further areas of applicability will become apparent from the description provided herein. It should be understood that the description and specific examples are intended for purposes of illustration only and are not intended to limit the scope of the present disclosure.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic view of boron neutron capture reaction.

FIG. 2 is a nuclear reaction formula of ¹⁰B (n,α) ⁷Li neutron capture.

FIG. 3 is a plan view showing an exemplary beam diagnosis system for a neutron capture therapy system according to the description which follows.

FIG. 4 is a logic diagram showing the beam diagnosis system for the neutron capture therapy system of FIG. 3.

FIG. 5 is also a plan view showing another exemplary first neutron beam monitoring device in the beam diagnosis system.

FIG. 6 is a plan view of a radiation detection system, used for detecting γ rays instantly emitted under neutron beam irradiation, in the beam diagnosis system.

FIG. 7 is an exemplary of a function relationship graph between boron concentration and tumor dose.

The drawings described herein are for illustrative purposes only of selected embodiments and not all possible implementations, and are not intended to limit the scope of the present disclosure. Corresponding reference numerals indicate corresponding parts throughout the several views of the drawings.

DETAILED DESCRIPTION

The following description of the preferred embodiments is merely exemplary in nature and is in no way intended to limit the invention, its application, or uses.

Neutron capture therapy (NCT) has been increasingly practiced as an effective cancer curing means in recent years, and BNCT is the most common. Neutrons for NCT may be supplied by nuclear reactors or accelerators. Take AB-BNCT for example, its principal components include, in general, an accelerator for accelerating charged particles (such as protons and deuterons), a target, a heat removal system and a beam shaping assembly. The accelerated charged particles interact with the metal target to produce the neutrons, and suitable nuclear reactions are always determined according to such characteristics as desired neutron yield and energy, available accelerated charged particle energy and current and materialization of the metal target, among which the most discussed two are ⁷Li (p, n) ⁷Be and ⁹Be (p, n) ⁹B and both are endothermic reaction. Their energy thresholds are 1.881 MeV and 2.055 MeV respectively. Epithermal neutrons at a keV energy level are considered ideal neutron sources for BNCT. Theoretically, bombardment with lithium target using protons with energy slightly higher than the thresholds may produce neutrons relatively low in energy, so the neutrons may be used clinically without many moderations. However, Li (lithium) and Be (beryllium) and protons of threshold energy exhibit not high action cross section. In order to produce sufficient neutron fluxes, high-energy protons are usually selected to trigger the nuclear reactions.

The target, considered perfect, is supposed to have the advantages of high neutron yield, a produced neutron energy distribution near the epithermal neutron energy range (see details thereinafter), little strong-penetration radiation, safety, low cost, easy accessibility, high temperature resistance etc. But in reality, no nuclear reactions may satisfy all requests. The target in these embodiments of the present disclosure is made of lithium. However, well known by those skilled in the art, the target materials may be made of other metals besides the above-mentioned.

Requirements for the heat removal system differ as the selected nuclear reactions. ⁷Li (p, n) ⁷Be asks for more than ⁹Be (p, n) ⁹B does because of low melting point and poor thermal conductivity coefficient of the metal (lithium) target. In these embodiments of the present disclosure is ⁷Li (p, n) ⁷Be.

No matter BNCT neutron sources are from the nuclear reactor or the nuclear reactions between the accelerator charged particles and the target, only mixed radiation fields are produced, that is, beams include neutrons and photons having energies from low to high. As for BNCT in the depth of tumors, except the epithermal neutrons, the more the residual quantity of radiation ray is, the higher the proportion of nonselective dose deposition in the normal tissue is. Therefore, radiation causing unnecessary dose should be lowered down as much as possible. Besides air beam quality factors, dose is calculated using a human head tissue prosthesis in order to understand dose distribution of the neutrons in the human body. The prosthesis beam quality factors are later used as design reference to the neutron beams, which is elaborated hereinafter.

The International Atomic Energy Agency (IAEA) has given five suggestions on the air beam quality factors for the clinical BNCT neutron sources. The suggestions may be used for differentiating the neutron sources and as reference for selecting neutron production pathways and designing the beam shaping assembly, and are shown as follows:

Epithermal neutron flux >1×10⁹ n/cm²s

Fast neutron contamination <2×10⁻¹³ Gy-cm²/n

Photon contamination <2×10⁻¹³ Gy-cm²/n

Thermal to epithermal neutron flux ratio <0.05

Epithermal neutron current to flux ratio >0.7

Note: the epithermal neutron energy range is between 0.5 eV and 40 keV, the thermal neutron energy range is lower than 0.5 eV, and the fast neutron energy range is higher than 40 keV.

1. Epithermal Neutron Flux

The epithermal neutron flux and the concentration of the boronated pharmaceuticals at the tumor site codetermine clinical therapy time. If the boronated pharmaceuticals at the tumor site are high enough in concentration, the epithermal neutron flux may be reduced. On the contrary, if the concentration of the boronated pharmaceuticals in the tumors is at a low level, it is required that the epithermal neutrons in the high epithermal neutron flux should provide enough doses to the tumors. The given standard on the epithermal neutron flux from IAEA is more than 10⁹ epithermal neutrons per square centimeter per second. In this flux of neutron beams, therapy time may be approximately controlled shorter than an hour with the boronated pharmaceuticals. Thus, except that patients are well positioned and feel more comfortable in shorter therapy time, and limited residence time of the boronated pharmaceuticals in the tumors may be effectively utilized.

2. Fast Neutron Contamination

Unnecessary dose on the normal tissue produced by fast neutrons are considered as contamination. The dose exhibit positive correlation to neutron energy, hence, the quantity of the fast neutrons in the neutron beams should be reduced to the greatest extent. Dose of the fast neutrons per unit epithermal neutron flux is defined as the fast neutron contamination, and according to IAEA, it is supposed to be less than 2*10⁻¹³ Gy-cm²/n.

3. Photon Contamination (Gamma-Ray Contamination)

Gamma-ray long-range penetration radiation will selectively result in dose deposit of all tissues in beam paths, so that lowering the quantity of gamma-ray is also the exclusive requirement in neutron beam design. Gamma-ray dose accompanied per unit epithermal neutron flux is defined as gamma-ray contamination which is suggested being less than 2*10⁻¹³ Gy-cm²/n according to IAEA.

4. Thermal to Epithermal Neutron Flux Ratio

The thermal neutrons are so fast in rate of decay and poor in penetration that they leave most of energy in skin tissue after entering the body. Except for skin tumors like melanocytoma, the thermal neutrons serve as neutron sources of BNCT, in other cases like brain tumors, the quantity of the thermal neutrons has to be lowered. The thermal to epithermal neutron flux ratio is recommended at lower than 0.05 in accordance with IAEA.

5. Epithermal Neutron Current to Flux Ratio

The epithermal neutron current to flux ratio stands for beam direction, the higher the ratio is, the better the forward direction of the neutron beams is, and the neutron beams in the better forward direction may reduce dose surrounding the normal tissue resulted from neutron scattering. In addition, treatable depth as well as positioning posture is improved. The epithermal neutron current to flux ratio is better of larger than 0.7 according to IAEA.

The prosthesis beam quality factors are deduced by virtue of the dose distribution in the tissue obtained by the prosthesis according to a dose-depth curve of the normal tissue and the tumors. The three parameters as follows may be used for comparing different neutron beam therapy effects.

1. Advantage Depth

Tumor dose is equal to the depth of the maximum dose of the normal tissue. Dose of the tumor cells at a position behind the depth is less than the maximum dose of the normal tissue, that is, boron neutron capture loses its advantages. The advantage depth indicates penetrability of neutron beams. Calculated in cm, the larger the advantage depth is, the larger the treatable tumor depth is.

2. Advantage Depth Dose Rate

The advantage depth dose rate is the tumor dose rate of the advantage depth and also equal to the maximum dose rate of the normal tissue. It may have effects on length of the therapy time as the total dose on the normal tissue is a factor capable of influencing the total dose given to the tumors. The higher it is, the shorter the irradiation time for giving a certain dose on the tumors is, calculated by cGy/mA-min.

3. Advantage Ratio

The average dose ratio received by the tumors and the normal tissue from the brain surface to the advantage depth is called as advantage ratio. The average ratio may be calculated using dose-depth curvilinear integral. The higher the advantage ratio is, the better the therapy effect of the neutron beams is.

To provide comparison reference to design of the beam shaping assembly, we also provide the following parameters for evaluating expression advantages and disadvantages of the neutron beams in the embodiments of the present disclosure except the air beam quality factors of IAEA and the abovementioned parameters.

1. Irradiation time<=30 min (proton current for accelerator is 10 mA)

2. 30.0RBE-Gy treatable depth>=7 cm

3. The maximum tumor dose>=60.0RBE-Gy

4. The maximum dose of normal brain tissue<=12.5RBE-Gy

5. The maximum skin dose<=11.0RBE-Gy

Note: RBE stands for relative biological effectiveness. Since photons and neutrons express different biological effectiveness, the dose above should be multiplied with RBE of different tissues to obtain equivalent dose.

Referring to FIG. 3 and FIG. 4, one aspect of the subject disclosure is to improve the accuracy of a neutron beam irradiation dose for a neutron capture therapy system and to provide a beam diagnostic system which can be used in a neutron capture therapy system to perform fault diagnosis. Provided in one embodiment is a beam diagnostic system for a neutron capture therapy system.

The neutron capture therapy system includes an accelerator 10, a beam expanding device 20, a charged particle beam inlet for passing a charged particle beam P, the charged particle beam P, a neutron beam generating unit T generating a neutron beam N by means of a nuclear reaction with the charged particle beam P, a beam shaping assembly 30 for adjusting flux and quality of the neutron beam generated by the neutron beam generating unit T, a beam outlet 40 adjoining to the beam shaping assembly 30, a irradiated body 50 irradiated by a beam emitted out from the beam outlet 40, and a cooling device 60 for putting a cooling medium at the neutron beam generating unit T to cool the neutron beam generating unit T. The accelerator 10 is used for accelerating the charged particle beam P, and may be an accelerator suitable for an accelerator-type neutron capture therapy system such as a cyclotron or a linear accelerator. The charged particle beam P here is a proton beam. The beam expanding device 20 is disposed between the accelerator 10 and the neutron beam generating unit T. The charged particle beam inlet abuts the neutron beam generating unit T and is accommodated in the beam shaping assembly 30. Three arrows between the neutron beam generating unit T and the beam expanding device as shown in FIG. 3 serve as the charged particle beam inlet. The neutron beam generating unit T is accommodated in the beam shaping assembly 30. The neutron beam generating unit T here is lithium metal. The beam shaping assembly 30 includes a reflector 31, a moderator 32 which is surrounded by the reflector 31 and abuts the neutron beam generating unit T, a thermal neutron absorber 33 abutting the moderator 32, and a radiation shield 34 disposed in the beam shaping assembly 30. The neutron beam generating unit T and the charged particle beam P emitted from the charged particle beam inlet perform a nuclear reaction to generate the neutron beam N. The neutron beam defines a principal axis, the moderator 32 moderates neutrons generated by the neutron beam generating unit T to an epithermal neutron energy region, the reflector 31 guides the neutrons deviating from the principal axis back to the principal axis so as to improve the intensity of an epithermal neutron beam, the thermal neutron absorber 33 is used for absorbing thermal neutrons so as to avoid excess doses caused with normal tissues of a superficial layer during therapy, and the radiation shield 34 is used for shielding leaked neutrons and photons so as to reduce a normal tissue dose of a non-irradiation region. The beam outlet 40 may also be referred to as a neutron beam convergence part or a collimator, which reduces the widths of neutron beams so as to gather the neutron beams. The neutron beams emitted from the beam outlet 40 irradiate a target part of the irradiated body 50.

The beam diagnostic system includes a charged particle beam diagnostic device and a neutron beam diagnostic device, and the beam diagnostic system is used for simultaneously diagnosing whether the neutron capture therapy system and/or the beam diagnostic system is malfunctioning. The beam diagnostic system improves the accuracy of a neutron beam irradiation dose by detecting the charged particle beam and the neutron beam simultaneously. In addition, the beam diagnostic system is used for judging which devices and/or components in the neutron capture therapy system are abnormal by means of a series of detection results, or judging whether a detection device in the beam diagnostic system is abnormal. Thus, not only the accuracy of the neutron beam irradiation dose is improved with a purpose, but also the maintenance time and cost are greatly reduced.

The charged particle beam diagnostic device further includes a first current detection device 100 for detecting the intensity and stability of the charged particle beam P before entering the charged particle beam inlet, and a second current detection device 200 for detecting the intensity and change situation of the charged particle beam P interacting with the neutron beam generating unit T; the beam diagnostic system further includes a temperature detection device 300 for detecting the temperature of the cooling device 60 so as to obtain a situation of the cooling device 60 and the neutron beam N generating of the neutron beam generating unit T; the neutron beam diagnostic device further includes a first neutron beam monitoring device 400 which is used for detecting the intensity change and space distribution of the neutron beam N in the beam shaping assembly 30 and is embedded in the beam shaping assembly 30, and a second neutron beam monitoring device 500 which is used for detecting the intensity change and space distribution of the neutron beam N at the beam outlet 40 and is embedded at the beam outlet 40; and the beam diagnostic system further includes a displacement detection device 600 for diagnosing whether the irradiated body 50 displaces. The first neutron beam monitoring device 400 may be provided with two neutron beam monitoring members namely a first neutron beam monitoring member 401 and a second neutron beam monitoring member 402; the second neutron beam monitoring device 500 may be provided with two neutron beam monitoring members namely a third neutron beam monitoring member 501 and a fourth neutron beam monitoring member 502; and the displacement detection device 600 may be provided with two displacement detection members namely a first displacement detection member 601 and a second displacement detection member 602.

Although in the subject disclosure, the first neutron beam monitoring device 400, the second neutron beam monitoring device 500 and the displacement detection device 600 are provided with two respective monitoring/detection members separately, it is well known to a person skilled in the art that the number of the monitoring/detection members may be set as required. For example, there may be four, six or eight monitoring/detection members. As long as a neutron beam monitoring member is embedded into the beam shaping assembly (or near the beam shaping assembly) and/or in the beam outlet (or near the beam outlet) and can be used for detecting the intensity change and space distribution of the neutron beam, the neutron beam monitoring member may be selected for use. As long as a displacement detection member is disposed in the irradiated body (or near the irradiated body) and can be used for detecting the displacement change of the irradiated body, the displacement detection member may be selected for use. In addition, the placement positions of the monitoring/detection members are not strictly limited. It is only required to make the placement positions able to achieve corresponding detection functions.

By means of such setting, various detection devices are disposed from the source of the accelerator to the terminal of the irradiated body. The detection devices are used for judging whether each key component of the neutron capture therapy system or the detection devices themselves are abnormal. The detection devices may be disposed from the source of the accelerator to the terminal of the irradiated body in such a way that a detection device is disposed at a vacuum tube at the source of the accelerator, a detection device is disposed at the neutron beam generating unit, a detection device is disposed at the cooling device which abuts the neutron beam generating unit and is used for cooling the neutron beam generating unit, a detection device is disposed in the beam shaping assembly, a detection device is disposed at the beam outlet, and a detection device is disposed at the irradiated body.

In the subject disclosure, the first current detection device 100 is a Faraday cup electrometer, which is a cup-shaped metal vacuum detector for measuring the incident intensity and stability of the charged particle beam, wherein a measured current may be used for determining the quantity of charged particle beams. When the charged particle beam enters the Faraday cup electrometer, a current will be generated. A successive charged particle beam with a single charge is calculated by means of FORMULA 1, where N is the quantity of charged particles, t is time (in second), I is a measured current (in ampere), and e is an elementary charge (about 1.60×10¹⁹ coulombs). It is estimable that if the measured current is 10⁻⁹ A (1 nA), about six billion charged particles are collected by the Faraday cup electrometer.

$\begin{matrix} {\frac{N}{t} = \frac{I}{e}} & \left( {{FORMULA}\mspace{14mu} 1} \right) \end{matrix}$

Certainly, it is well known to a person skilled in the art that the first current detection device 100 may be any detection device suitable for measuring the incident intensity and stability of the charged particle beam at the vacuum tube of the accelerator, such as a wall current monitor and a beam current transformer.

The wall current monitor bridges sampling resistors to two ends of a ceramic isolation segment, a voltage sampling signal can be obtained when a beam mirror current flows through the sampling resistors, and the voltage sampling signal is calculated by means of FORMULA 2, where V is a detected voltage value, I_(b) is a charged particle beam current, Z may be equivalent to resistance under a specific frequency, and a wall current monitor equivalent circuit is a parallel RLC circuit, as shown in FORMULA 3. Therefore, the current of the charged particle beam within a certain period of time t can be calculated according to the detected voltage value.

$\begin{matrix} {V = {{- {I_{b}(t)}}Z}} & \left( {{FORMULA}\mspace{14mu} 2} \right) \\ {\frac{1}{Z} = {\frac{1}{R} + \frac{1}{j\; \omega \; L} + {j\; \omega \; C}}} & \left( {{FORMULA}\mspace{14mu} 3} \right) \end{matrix}$

The beam current transformer is used for coupling a current signal by utilizing a secondary winding on a magnetic core to obtain the current of an original charged particle beam by analyzing the signal, such as AC Current Transformer (ACCT), Fast Current Transformer (FCT), Tuned Current Transformer (TCT), Integrated Current Transformer (ICT) and DC Current Transformer (DCCT). Due to numerous varieties, the beam current transformers will not be enumerated one by one hereinafter. Only the DCCT is taken as an example. The DCCT modulates a DC signal to be detected to secondary harmonics of an excitation signal for detection by adopting a nonlinear magnetic modulation component.

In the subject disclosure, the second current detection device 200 is a galvanometer, one end being electrically connected to the neutron beam generating unit T and the other one being grounded, so as to form a detection loop, thereby obtaining a current on the neutron beam generating unit T when the charged particle beam P bombards the neutron beam generating unit T. The galvanometer is made according to a principle that a current-carrying coil deflects in a magnetic field under the action of torque. A coil in a common electric meter is placed on a bearing, keeps balanced by using a balance spring, and the deflection is indicated by a pointer. The bearing is frictional, so the measured current cannot be too weak. In the galvanometer, a very thin metal suspension wire instead of the bearing is suspended in the magnetic field. The suspension wire is thin and long, and a resisting torque is small, so the coil can be obviously deflected when a very weak current passes through the coil. Thus, the galvanometer is more sensitive than a common electric meter, and can measure a micro-current (10⁻⁷-10⁻¹⁰ A) or a micro-voltage (10⁻³-10⁻⁶V) such as a light current, a physiological current and a thermal electromotive force. The first record about a nerve action potential was made by using this type of instrument.

Certainly, it is well known to a person skilled in the art that the second current detection device 200 may be any detection device suitable for detecting, near the neutron beam generating unit, the intensity and change situations of the charged particle beam interacting with the neutron beam generating unit, such as an electric meter and a voltmeter.

In the subject disclosure, the temperature detection device 300 is a thermocouple. Both ends of two conductors (referred to as thermocouple wires or thermal electrodes) with different components are connected into a loop. When the temperatures of junctions are different, an electromotive force will be generated in the loop, the phenomenon is referred to as a thermo-electric effect, the electromotive force is referred to as a thermal electromotive force. The thermocouple performs temperature measurement by utilizing the principle, wherein an end directly used for measuring a medium temperature is referred to as a working end (or measurement end) whilst the other end is referred to as a cold end (or compensation end). The cold end is connected with a display instrument or an auxiliary instrument, and the display instrument will indicate the thermal electromotive force generated by the thermocouple.

Certainly, it is well known to a person skilled in the art that the temperature detection device 300 may be any detection device suitable for being disposed in the cooling device or near the cooling device and used for detecting the temperature of the cooling device so as to obtain a situation of the cooling device and the neutron beam generating of the neutron beam generating unit, such as a resistance thermometer, which measures a temperature according to a rule of varying of conductor resistance along with temperature by using a temperature sensor made of a material characterized by varying of given resistance along with temperature.

A common neutron beam monitoring device for real-time detection may have two different detection principles, namely an ionization chamber and a scintillator detector. Those adopting ionization chamber structures as substrates include He-3 proportional counter, BF₃ proportional counter, fission chamber and boron ionization chamber. The scintillator detector may be divided into organic and inorganic materials, and for the purpose of detecting thermal neutrons, the scintillator detector mainly adds high thermal neutron capture section elements such as Li or B. In short, most of neutron energies detected by this type of detectors are the thermal neutrons, which all rely on heavy charged particles and nuclear fission fragments released by means of a capture or nuclear fission reaction between elements and neutrons, a great number of ion pairs are generated in the ionization chamber or the scintillator detector, and after the charges are collected, a current signal may be converted into a voltage pulse signal via appropriate circuit conversion. A neutron signal and a γ signal can be easily distinguished from each other by analyzing the magnitude of a voltage pulse. In a high-intensity neutron field such as a BNCT, the gas pressure of the ionization chamber, the concentration of coating of fissionable materials or boron or the concentration of the high neutron capture section elements in the scintillator detector can be appropriately reduced, so the sensitivity to neutrons can be effectively reduced, and the situation of signal saturation is avoided.

The first neutron beam monitoring device 400 may be a fission chamber. When passing through the fission chamber, a neutron beam ionizes gas molecules inside the fission chamber or a wall portion of the fission chamber to generate an electron and an ion with a positive charge, the electron and the positive charge ion are referred to as the aforementioned ion pair. The interior of the fission chamber has an external electric field high voltage, so the electron moves toward a central anode wire, and the positive charge ion moves toward a surrounding cathode wall, thus generating an electronic pulse signal which can be measured. An energy needed for generating an ion pair by gas molecules is referred to as an average ionizing energy, the value varying with a gas type. For example, the average ionizing energy of air is about 34 eV. If a neutron beam of 340 keV exists, the air will generate about 10k ion pairs.

Certainly, it is well known to a person skilled in the art that the first neutron beam monitoring device 400 may be any detection device suitable for being embedded in the beam shaping assembly and used for detecting the intensity change and space distribution of the neutron beam in the beam shaping assembly, such as He-3 proportional counter, BF3 proportional counter, boron ionization chamber and scintillator detector.

The second neutron beam monitoring device 500 may be a scintillator detector, and after certain materials absorbing energy, visible light will be emitted, and the materials are referred to as scintillating materials. It utilizes ionizing radiation to excite an electron in a crystal or molecule to an exciting state, fluorescent light emitted when the electron returns to a base state is used for monitoring a neutron beam after being collected. The visible light emitted after the scintillator detector interacts with the neutron beam can be converted into an electron by utilizing a photomultiplier, and the electron is multiplied and amplified, wherein the multiplication and amplification rate of the electron can reach 107 to 108 usually. The quantity of electrons output from an anode is in direct proportion to energy of an incident neutron beam, and therefore the scintillator detector can measure the energy of the neutron beam.

Certainly, it is well known to a person skilled in the art that the second neutron beam monitoring device 500 may be any detection device suitable for being disposed in the beam outlet or near the beam outlet and used for detecting the intensity change and space distribution of a neutron beam at the beam outlet, such as He-3 proportional counter, BF₃ proportional counter, boron ionization chamber and fission chamber.

The displacement detection device 600 may be an infrared signal detector, the infrared detector works by detecting an infrared ray emitted by a human body. The detector collects external infrared radiation and further gathers the external infrared radiation to an infrared sensor. The infrared sensor usually adopts a pyroelectric element. The element will release a charge outward after receiving an infrared radiation temperature change, and will give an alarm after detection. The detector aims to detect human body radiation. A radiation-sensitive element must be very sensitive to infrared radiation of which a wavelength is about 10 μm.

Certainly, it is well known to a person skilled in the art that the displacement detection device 600 may be any detection device suitable for being used for detecting the displacement change of the irradiated body, such as a displacement sensor. The displacement sensor determines whether the irradiated body moves according to the displacement change of the irradiated body relative to a certain reference substance. It is also well known to a person skilled in the art that the displacement detection device not only can be used for detecting the displacement change of the irradiated body, but also can be used for detecting the displacement change of a supporting piece for fixing the irradiated body and/or a therapy table, thereby indirectly knowing the displacement change of the irradiated body.

It is well known to a person skilled in the art that the number of first current detection devices, the number of second current detection devices, the number of temperature detection devices, the number of first neutron beam monitoring devices, the number of second neutron beam monitoring devices, the number of displacement detection devices, and detection elements are not limited. The numbers and the detection elements in the subject disclosure are only taken as an example.

According to a function relationship between detection results of detection and/or monitoring devices, malfunctioning components can be obviously enumerated. Several fault diagnosis situations made according to corresponding detection results will be enumerated hereinafter.

When it is detected that any one detection or monitoring device of the first current detection device 100, the second current detection device 200, the temperature detection device 300, the first neutron beam monitoring device 400 and the second neutron beam monitoring device 500 is abnormal whilst all other detection or monitoring devices are normal, it is concluded that the abnormal detection or monitoring device itself is malfunctioning; and when it is detected that the displacement detection device 600 is abnormal whilst all other detection or monitoring devices are normal, it is concluded that the displacement of the irradiated body 50 is changed or the displacement detection device 600 is malfunctioning.

When it is detected that the first current detection device 100, the second current detection device 200, the temperature detection device 300, the first neutron beam monitoring device 400 and the second neutron beam monitoring device 500 are all abnormal, it is concluded that the accelerator 10 is malfunctioning.

When it is detected that the second current detection device 200, the temperature detection device 300, the first neutron beam monitoring device 400 and the second neutron beam monitoring device 500 are all abnormal whilst both the first current detection device 100 and the displacement detection device 600 are normal, it is concluded that the beam expanding device 20 is malfunctioning.

When it is detected that the temperature detection device 300, the first neutron beam monitoring device 400 and the second neutron beam monitoring device 500 are all abnormal whilst the first current detection device 100, the second current detection device 200 and the displacement detection device 600 are all normal, it is concluded that the neutron beam generating unit T and/or the cooling device 60 is malfunctioning.

When it is detected that both the first neutron beam monitoring device 400 and the second neutron beam monitoring device 500 are abnormal whilst the first current detection device 100, the second current detection device 200, the temperature detection device 300 and the displacement detection device 600 are all normal, it is concluded that the beam shaping assembly 30 is malfunctioning.

When it is detected that any one of monitoring results of the first neutron beam monitoring member 401 and the second neutron beam monitoring member 402 and/or any one of the third neutron beam monitoring member 501 and the fourth neutron beam monitoring member 502 is abnormal, it is concluded that the abnormal neutron beam monitoring member itself is malfunctioning or the uniformity of the neutron beam is abnormal.

Certainly, it is well known to a person skilled in the art that the aforementioned fault diagnosis situations made according to the detection results are only some enumerated common situations, there are many permutations and combinations, and the above modes can be still adopted to judge which neutron capture therapy systems or detection devices are malfunctioning and which faults are included. Here, although they are not enumerated one by one, changes made according to such a spirit still fall within the summary of the present disclosure.

The beam diagnostic system includes a control device 700 with a control unit 710, the control unit 710 sends a human-perceivable signal according to a detection result of the beam diagnostic system so as to confirm a next operation of the neutron capture therapy system. The human-perceivable signal may be a signal which can be perceived by human functional organs such as auditory sense, visual sense, tactile sense or smell sense. For example, the signal is one or more forms in various signals such as a sound-making alarm, an alarm lamp, a vibrating signal and a pungent smell emitting signal. The control device 700 may further includes a display unit 720, the display unit 720 is used for displaying a detection result of the detection device and/or a fault diagnosis situation made according to the detection result on display equipment, and the display equipment may be common display equipment such as a television or a liquid crystal display. According to a feedback from the control device, an operator can easily determine a malfunctioning component, thereby maintaining the neutron capture therapy system and/or the beam diagnostic system with a purpose.

Further referring to FIG. 5, it shows another embodiment of the first neutron beam monitoring device. The first neutron beam monitoring device is marked by number 400′, the devices/members as shown in the figure, which are identical to those in FIG. 3, are still marked by the same numeric identifiers, and for convenience of display, the cooling device and other monitoring/detection devices are omitted.

The first neutron beam monitoring device 400′ may include one or more neutron beam monitoring members, it can be disposed near the beam shaping assembly 30 to detect a neutron beam overflowing through the neutron beam generating unit T so as to detect the intensity change and space distribution of the neutron beam in a direct manner, and can also be disposed near the beam shaping assembly 30 to detect a γ ray generated by interaction between the charged particle beam P and the neutron beam generating unit T. The intensity change and space distribution of the neutron beam can be indirectly detected according to a function relationship between the γ ray and the neutron beam. The control device 700′ includes a control unit 710′ and a display unit 720′. The display unit 720′ is used for displaying a detection result of a detection device 400′ and/or a fault diagnosis situation made according to the detection result on display equipment, and the display equipment may be common display equipment such as a television or a liquid crystal display. According to a feedback from the control device, an operator can easily determine a malfunctioning component, thereby executing a next operation on the accelerator 10 with a purpose.

Further refer to FIG. 6 which is a plan view of the radiation detection system, used for detecting γ rays instantly emitted under neutron beam irradiation, in the beam diagnosis system, the radiation detection device (namely the device for detecting γ rays instantly emitted under neutron beam irradiation) is marked with the label 800, devices/components which are also included in FIG. 3 are marked with the same labels, and the cooling device and other detection/monitoring devices are omitted for the display purpose.

The γ ray detection device 800 includes one or more γ ray detection components, namely a fission chamber or scintillator detector for detecting γ rays. The γ rays are instantly emitted after the boron neutron capture reaction under neutron beam irradiation. Once the measured γ count (the 0.48 MeV generated when the boron neutron capture reaction occurs is only an example) in the preset energy zone is known, the boron concentration value can be calculated according to the function relationship between γ rays and boron concentration. The control device 700″ includes a control part 710″ and a display part 720″. The display part 720″ is used for displaying the detection result of the detection device 800 and/or the failure diagnosis condition obtained according to the detection result on a display device, and the display device can be a television, a liquid crystal display, or other common display devices. According to the feedback of the control device, an operator can easily confirm a failure component, so as to perform corresponding operation on the accelerator 10.

The γ rays instantly emitted under neutron beam irradiation are γ rays generated when a neutron capture nuclear reaction occurs between the neutron beam and other elements, and other elements are not limited to boron-10 and elements well known in the art capable of generating γ rays when a neutron capture nuclear reaction occurs are also included. In the embodiment of the present invention, the γ rays instantly emitted under neutron beam irradiation are γ rays generated when a boron neutron capture reaction occurs between the neutron beam and boron-10.

Preferably, the boron concentration value is calculated by means of the Formula A:

$\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$

wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k is calculated by means of the Formula B:

$\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$

wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) is calculated by means of the Formula C:

B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C)

wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.

For accurately judging which detection device or monitoring device breaks down, when the detection values below and the standard values have a big difference, a corresponding detection device or monitoring device can be concluded to be abnormal.

The tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula D:

D _(T)(t)=D _(B)(t)+D _(n)(t)+D(t)  (Formula D)

wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) is calculated by means of the Formula E:

$\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} E} \right) \end{matrix}$

The D_(n)(t) is calculated by means of the Formula F:

$\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$

The D_(γ)(t) is calculated by means of the Formula G:

 

wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through reactions except boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in the treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.

Preferably, the tumor dose rate at the time t can also be calculated by means of the Formula H:

 

wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) is calculated by means of the Formula I, and C is a calculated value calculated by means of the Formula J:

 

wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, σ is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.

FIG. 7 shows the function relationship between boron concentration B_(blood)(t) and tumor dose B_(tumor)(t) in the embodiment. Preferably, based on the fact that neutron radiation source intensity is 1.7×10¹¹ n/s, the non-linear relationship between boron concentration and tumor dose is calculated by means of the Formula K, in this way, the non-linear relationship between boron concentration and tumor dose can be effectively corrected in the neutron capture therapy system, and the accuracy of the treatment plan can be improved.

B _(tumor)(t)=0.01643+0.8034×B _(blood)(t)−0.00167×B _(blood)(t)²−2.42362×10⁻⁵ ×B _(blood)(t)³   (Formula K)

As is well known to a person skilled in the art, the function relationship between boron concentration B_(blood)(t) and tumor dose B_(tumor)(t) as shown in FIG. 7 is not limited to the Formula K, as long as the non-linear function relationship between B_(blood)(t) and tumor dose B_(tumor)(t) is figured out according to an empirical value. The function relationship between boron concentration B_(blood)(t) and tumor dose B_(tumor)(t) as shown in FIG. 7 is not limited to the fact that neutron radiation source intensity is 1.7×10¹¹ n/s either, and different functional relationships can be obtained based on different neutron radiation source intensities from experience. The neutron capture therapy system according to the embodiment of the present invention can correct the non-linear function relationship between boron concentration and tumor dose, so as to improve the accuracy of the treatment plan.

It needs to be pointed out that both the neutron monitoring device and the radiation detection device need to be subjected to hysteresis effect correction.

The radiation detection method for the neutron capture therapy system can increase the accuracy of neutron beam irradiation dose of the neutron capture therapy system and find out a failure position in time, and the radiation detection method corresponds to the radiation detection system.

To sum up, it is not limited whether the first neutron beam monitoring device is disposed in the beam shaping assembly or near the beam shaping assembly, and any detection device which can be used for detecting the intensity change and space distribution of the neutron beam in the beam shaping assembly at the arrangement position may be selected.

The radiation detection system for the neutron capture therapy system and the corresponding radiation detection method disclosed by the present disclosure are not limited to the contents in the foregoing embodiments and the structures shown in the drawings. All obvious changes, replacements or modifications made on materials, shapes and positions of members on the basis of the present disclosure fall within the scope of protection of the present disclosure. 

What is claimed is:
 1. A radiation detection system for a neutron capture therapy system comprising: a charged particle beam; a charged particle beam inlet allowing the charged particle beam to pass through; a neutron beam generating unit generating a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam; a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit; and a beam outlet adjacent to the beam shaping assembly; wherein the radiation detection system comprises a radiation detection device for real-time detection of γ rays instantly emitted under neutron beam irradiation.
 2. The radiation detection system for the neutron capture therapy system according to claim 1, wherein the neutron capture therapy system further comprises an accelerator for accelerating the charged particle beam, the radiation detection system further comprises a control device for emitting a human perception signal according to a detection result of the radiation detection device so as to confirm the next operation of the neutron capture therapy system, and wherein the control device comprises a control part and a display part, and the control part displays the detection result of the radiation detection system through the display part and feeds the detection result back to the accelerator so as to confirm the next operation of the accelerator.
 3. The radiation detection system for the neutron capture therapy system according to claim 2, wherein the radiation detection device is a fission chamber or a scintillator detector for detecting γ rays, and the radiation detection system calculates a boron concentration value through a detected γ signal.
 4. The radiation detection system for the neutron capture therapy system according to claim 3, wherein the boron concentration value is calculated by means of a Formula A: $\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$ wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value obtained after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k is calculated by means of the Formula B: $\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$ wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value obtained after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) is calculated by means of the Formula C: B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C) wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.
 5. The radiation detection system for the neutron capture therapy system according to claim 4, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula D: D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D) wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) is calculated by means of the Formula E: $\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{Blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} E} \right) \end{matrix}$ The D_(n)(t) is calculated by means of a Formula F: $\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$ The D_(γ)(t) is calculated by means of a Formula G: $\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$ wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.
 6. The neutron capture therapy system according to claim 4, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula H: $\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{nbcap},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$ wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) is calculated by means of the Formula I, and C is a calculated value calculated by means of the Formula J: $\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{B}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$ wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, G is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.
 7. A radiation detection method for a neutron capture therapy system, wherein the neutron capture therapy system comprises: a charged particle beam; a charged particle beam inlet allowing the charged particle beam to pass through; a neutron beam generating unit generating a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam; a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron generation par, the neutron beam generating unit is contained in the beam shaping assembly; a beam outlet adjacent to the beam shaping assembly; and a radiation detection system comprising a radiation detection device, wherein the radiation detection method comprises a detection step of detecting γ rays instantly emitted under neutron beam irradiation in real time through the radiation detection device.
 8. The radiation detection method for the neutron capture therapy system according to claim 7, wherein the radiation detection system further comprises a control device, the control device comprises a control part and a display part, the detection method comprises a control step of controlling the next operation of the neutron capture therapy system through the control part according to a detection result obtained from the detection step; and the detection method further comprises a display step of displaying the detection result obtained from the detection step through the display part.
 9. The radiation detection method for the neutron capture therapy system according to claim 8, wherein the detection method comprises a calculation step of calculating a boron concentration value according to the detection result obtained from the detection step.
 10. The radiation detection method for the neutron capture therapy system according to claim 9, wherein the boron concentration value is calculated by means of the Formula A: $\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$ wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value obtained after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k is calculated by means of the Formula B: $\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$ wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) is calculated by means of a Formula C: B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C) wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.
 11. The radiation detection method for the neutron capture therapy system according to claim 10, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula D: D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D) wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) is calculated by means of the Formula E: $\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{20mu} E} \right) \end{matrix}$ The D_(n)(t) is calculated by means of the Formula F: $\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$ The D_(γ)(t) is calculated by means of the Formula G: $\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{s_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$ wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.
 12. The radiation detection method for the neutron capture therapy system according to claim 10, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula H: $\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{{nb}\; {cap}},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$ wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) is calculated by means of the Formula I, and C is a calculated value calculated by means of the Formula J: $\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{B}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$ wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, G is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device.
 13. A neutron capture therapy system comprising: a charged particle beam; a charged particle beam inlet allowing the charged particle beam to pass through; a neutron beam generating unit generating a neutron beam after a nuclear reaction occurs between the neutron beam generating unit and the charged particle beam; a beam shaping assembly for adjusting the flux and the quality of the neutron beam generated by the neutron beam generating unit; and a beam outlet adjacent to the beam shaping assembly; wherein the neutron capture therapy system corrects the non-linear relationship between boron concentration and tumor dose.
 14. The neutron capture therapy system according to claim 13, wherein the neutron capture therapy system comprises a radiation detection system, and wherein the radiation detection system comprises a radiation detection device for real-time detection of γ rays instantly emitted under neutron beam irradiation.
 15. The neutron capture therapy system according to claim 14, wherein the neutron capture therapy system further comprises an accelerator for accelerating the charged particle beam, the radiation detection system further comprises a control device for emitting a human perception signal according to a detection result of the radiation detection device so as to confirm the next operation of the neutron capture therapy system, and wherein the control device comprises a control part and a display part, and the control part displays the detection result of the radiation detection system through the display part and feeds the detection result back to the accelerator so as to confirm the next operation of the accelerator.
 16. The neutron capture therapy system according to claim 15, wherein the radiation detection device is a fission chamber or a scintillator detector for detecting γ rays, and the radiation detection system calculates a boron concentration value through a detected γ signal.
 17. The neutron capture therapy system according to claim 16, wherein the boron concentration value is calculated by means of a Formula A: $\begin{matrix} {{B(t)} = \frac{{GC}(t)}{k}} & \left( {{Formula}\mspace{14mu} A} \right) \end{matrix}$ wherein B(t) is the boron concentration value at the time t, the unit of B(t) is ppm, the unit of time t is s, k is a measured value, GC(t) is the value obtained after γ count existing in the background is deducted from the total γ count of a preset energy zone detected at the time t, and k is calculated by means of the Formula B: $\begin{matrix} {k = \frac{{GC}\left( t_{0} \right)}{B\left( t_{0} \right)}} & \left( {{Formula}\mspace{14mu} B} \right) \end{matrix}$ wherein B(t₀) is the boron concentration value at the time t₀, the unit of B(t₀) is ppm, the unit of time t₀ is s, GC(t₀) is the value obtained after γ count existing in the background is deducted from the total γ count of the preset energy zone detected at the time t₀, and B(t₀) is calculated by means of the Formula C: B(t ₀)=B _(blood)(t ₀)×R _(T/N)   (Formula C) wherein B_(blood)(t₀) is the boron concentration value in blood measured at the time t₀, the unit of B_(blood)(t₀) is ppm, and R_(T/N) is the ratio of boron concentration in a tumor capable of being acquired according to PET or experiment data or theoretical basis to boron concentration in normal tissue.
 18. The neutron capture therapy system according to claim 17, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula D: D _(T)(t)=D _(B)(t)+D _(n)(t)+D _(γ)(t)  (Formula D) wherein the unit of D_(T)(t) is w-Gy/s, D_(B)(t) is the boron dose rate at the time t, the unit of D_(B)(t) is w-Gy/s, D_(n)(t) is the neutron dose rate at the time t, the unit of D_(n)(t) is w-Gy/s, D_(γ)(t) is the photon dose rate at the time t, the unit of D_(γ)(t) is w-Gy/s, and D_(B)(t) is calculated by means of the Formula E: $\begin{matrix} {{D_{B}(t)} = {D_{B,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}} & \left( {{Formula}\mspace{20mu} E} \right) \end{matrix}$ The D_(n)(t) is calculated by means of a Formula F: $\begin{matrix} {{D_{n}(t)} = {D_{n,{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}}}} & \left( {{Formula}\mspace{14mu} F} \right) \end{matrix}$ The D_(γ)(t) is calculated by means of a Formula G: $\begin{matrix} {{D_{\gamma}(t)} = {{D_{\gamma,{nbcap},{ref}} \times \frac{S_{n}(t)}{s_{n,{ref}}}} + {D_{\gamma,{bcap},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)}}}} & \left( {{Formula}\mspace{14mu} G} \right) \end{matrix}$ wherein D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) are the given reference value or the corrected given reference value of the boron dose rate, the given reference value of the neutron dose rate, the given reference value of the dose rate of photons generated through non-boron neutron capture reaction, and the given reference value of the dose rate of photons generated through boron neutron capture reaction in a treatment plan system respectively, and the unit of D_(B,ref), D_(n,ref), D_(γ,nbcap,ref) and D_(γ,bcap,ref) is w-Gy/s; S_(n)(t) is the reading of neutron beam intensity of a neutron monitoring device at the time t, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; S_(n,ref) is a given value of neutron beam intensity or a corrected given value of neutron beam intensity in the treatment plan system; B_(blood)(t) is the boron concentration value of a measured blood sample at the time t, and the unit of B_(blood)(t) is ppm; B_(blood,ref) is a given value of boron concentration or a corrected given value of boron concentration in the treatment plan system, and the unit of B_(blood,ref) is ppm; and f(B_(blood)(t),B_(blood,ref)) is a set of functions precomputed according to a treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose.
 19. The neutron capture therapy system according to claim 17, wherein the tumor dose rate D_(T)(t) at the time t is calculated by means of the Formula H: $\begin{matrix} {{D_{T}(t)} = {{\frac{S_{n}(t)}{S_{n,{ref}}} \times \left( {D_{n,{ref}} + D_{\gamma,{{nb}\; {cap}},{ref}}} \right)} + {{S_{B}(t)} \times C \times \left( {D_{\gamma,{bcap},{ref}} + D_{B,{ref}}} \right)}}} & \left( {{Formula}\mspace{14mu} H} \right) \end{matrix}$ wherein S_(B)(t) is the reading of the radiation detection device at the time t, the unit of S_(B)(t) is count or reading capable of being selected by the radiation detection device, S_(B)(t) is calculated by means of the Formula I, and C is a calculated value calculated by means of the Formula J: $\begin{matrix} {{S_{B}(t)} = {N_{{NB},{ref}} \times \frac{S_{n}(t)}{S_{n,{ref}}} \times \frac{B_{blood}(t)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}(t)},B_{{blood},{ref}}} \right)} \times k_{BG} \times \sigma}} & \left( {{Formula}\mspace{14mu} I} \right) \\ {\mspace{79mu} {C = \frac{\frac{S_{n}\left( t_{0} \right)}{S_{n,{ref}}} \times \frac{B_{blood}\left( t_{0} \right)}{B_{{blood},{ref}}} \times {f\left( {{B_{blood}\left( t_{0} \right)},B_{{blood},{ref}}} \right)}}{S_{B}\left( t_{0} \right)}}} & \left( {{Formula}\mspace{14mu} J} \right) \end{matrix}$ wherein N_(NB,ref) is the reference value of the number of times of boron neutron capture reaction in the treatment plan, k_(BG) is a correction to a background, σ is the detection efficiency of the radiation detection device, S_(n)(t₀) is the reading of neutron beam intensity of the neutron monitoring device at the time t₀, and the unit of S_(n)(t) is count or reading capable of being selected by the radiation detection device; B_(blood)(t₀) is the boron concentration value of the measured blood sample at the time t₀, and the unit of B_(blood)(t₀) is ppm; f(B_(blood)(t₀),B_(blood,ref)) is a set of functions precomputed according to the treatment plan so as to correct the non-linear relationship between boron concentration and tumor dose; and S_(B)(t₀) is the reading, set at the initial stage of irradiation, of the neutron monitoring device, and the unit of S_(B)(t₀) is count or reading capable of being selected by the radiation detection device. 